EP1493385B1 - Portable detector device for measuring movements of a person - Google Patents
Portable detector device for measuring movements of a person Download PDFInfo
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- EP1493385B1 EP1493385B1 EP04103080A EP04103080A EP1493385B1 EP 1493385 B1 EP1493385 B1 EP 1493385B1 EP 04103080 A EP04103080 A EP 04103080A EP 04103080 A EP04103080 A EP 04103080A EP 1493385 B1 EP1493385 B1 EP 1493385B1
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- 230000033001 locomotion Effects 0.000 title claims abstract description 40
- 230000000694 effects Effects 0.000 claims abstract description 22
- 230000001766 physiological effect Effects 0.000 claims abstract description 11
- 238000000034 method Methods 0.000 abstract description 2
- 230000008569 process Effects 0.000 abstract description 2
- 230000036544 posture Effects 0.000 description 13
- 230000001133 acceleration Effects 0.000 description 9
- 238000005259 measurement Methods 0.000 description 9
- 238000004364 calculation method Methods 0.000 description 8
- 238000001914 filtration Methods 0.000 description 5
- 230000005484 gravity Effects 0.000 description 5
- 230000029058 respiratory gaseous exchange Effects 0.000 description 5
- 238000001514 detection method Methods 0.000 description 4
- 238000010606 normalization Methods 0.000 description 4
- 238000010200 validation analysis Methods 0.000 description 4
- 238000003745 diagnosis Methods 0.000 description 3
- 230000000241 respiratory effect Effects 0.000 description 3
- 230000000747 cardiac effect Effects 0.000 description 2
- 230000000737 periodic effect Effects 0.000 description 2
- 230000036387 respiratory rate Effects 0.000 description 2
- 238000012800 visualization Methods 0.000 description 2
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1116—Determining posture transitions
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/0205—Simultaneously evaluating both cardiovascular conditions and different types of body conditions, e.g. heart and respiratory condition
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1123—Discriminating type of movement, e.g. walking or running
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/16—Details of sensor housings or probes; Details of structural supports for sensors
- A61B2562/166—Details of sensor housings or probes; Details of structural supports for sensors the sensor is mounted on a specially adapted printed circuit board
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/02438—Detecting, measuring or recording pulse rate or heart rate with portable devices, e.g. worn by the patient
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6823—Trunk, e.g., chest, back, abdomen, hip
Definitions
- the subject of this invention is a portable detector for measuring movements of the wearer.
- Motion sensors have also been applied to various parts of the body to track the surrogate and sometimes to determine sleep, falling, etc.
- the complexity of postures and levels of human activity does not lend itself to a real analysis of the activity with the usual detectors, which are rather reserved for the detection of a single kind of events and programmed to ignore others, as far as possible.
- An improved portable detector comprises first signal processing means for distinguishing a component of the signal, due to an external activity of the carrier subject, of at least one component of the signal due to a physiological activity (the heart beat or breath especially).
- a physiological activity the heart beat or breath especially.
- the heartbeat and the breath are periodic movements, the intensity and frequency of which vary according to the level of activity of the wearer under particular conditions. Movements due to the outer activity of the wearer are generally low frequency; but not being periodic, they are included in a wider frequency band, and their intensity can vary greatly. Because of these frequency variations and moreover frequency band overlaps associated with these different movements, it is impossible to separate them by simple signal filtering. Satisfactory results, however, have been obtained by applying a non-stationary filter to the motion signal or signals and subtracting the filtered signal from the original signal (the raw signal or a pre-filtered signal to eliminate noise). : the signals of physiological origin come out quite well.
- Figure 1 illustrates the position of the detector on the person carrying
- Figure 2 the detector as a whole
- Figure 3 the treatment system.
- Figure 1 shows that the detector, labeled 1, is placed on the chest of a wearer 2. It could be placed on the abdomen or elsewhere.
- the detector 1 is miniature, which allows it to be worn comfortably and almost unnoticed, unlike others.
- the X, Y and Z axes are introduced for the convenience of the explanation and define a reference linked to the carrier 2, the X axis being directed forward, the Z axis to the feet and the Y axis to the right.
- the detector 1 may comprise a housing 3 containing three accelerometers all bearing the reference 4, three magnetometers all bearing the reference 5 and a processing system 6 to which accelerometers 4 and magnetometers 5 are connected by means of wires. to provide him with their signals.
- the accelerometers 4 each measure an acceleration component of the movement of the chest of the wearer 2 in one of the X, Y and Z axes respectively according to the direction of gravity; the magnetometers 5 do the same according to the direction of the Earth's magnetic field.
- the sensor 1 is held at a constant orientation against the skin or a wearer's garment 2 by glue, seam, clamping band, or any other suitable means.
- the signals from the accelerometers 4 or magnetometers 5 each pass through a normalization module 7 and are transmitted to two calculation modules 8 and 9 working both in parallel and in interaction, the first (8) of which calculates the component of the signals which is due to the external activity of the wearer 2 and the second (9) calculates the component of the signals due to physiological activity; this second module 9 comprises a submodule 10 assigned to the movements due to the heartbeat and a submodule 11 assigned to the movements due to breathing.
- the first calculation module 8 comprises a low-pass filter 12 which transmits the signal from the normalization module 7 to an activity analysis device 13, to a posture analysis device 14, to an analysis device activity level 15 and an estimator 16 of the activity component.
- the signal from the normalization module 7 reaches the submodules 10 and 11 after having passed through a subtractor 17, a validation module 18, and again, for the submodule 11, by a device of choice 19.
- the sub-module module 10 comprises a device for extracting the cardiac component 20, a frequency calculating device 21 and an examination device 22.
- the submodule 11 comprises a device for extracting the breathing component 23, a device for frequency calculation 24 and an output device 25.
- the normalization device 7 is of an ordinary kind which makes it possible to calibrate the signals, for example according to a linear law, in order to output normalized signals, which are proportional to the acceleration they undergo.
- the low-pass filter 12 serves to eliminate the high frequencies of the signal, which in practice only express noises.
- the activity analysis device 13 is not essential and its content may depend on the kinds of activities that try to diagnose, such as falling, sleeping, walking, changing position or others.
- the diagnosis can be made with several sensors 4 and 5.
- the posture analysis device 14 makes it possible to determine whether the wearer 2 is standing, sitting or lying by comparing the accelerations measured by the accelerometers 4.
- the wearer If the largest signal is measured by the accelerometer 4 X or the accelerometer 4 Y, the wearer is lying but he is sitting or standing if the Z acceleration is preponderant since the gravity is directed along this axis.
- the posture diagnosis is established if the acceleration ratios are greater than certain coefficients. If the carrier 2 is standing, the comparison of the measurements for the magnetometers 5 in X and Y can give direction in the cardinal points. The fall can be determined by a rapid rotation around a vertical axis or a rapid acceleration in rotation with respect to the gravitational field (measured with an accelerometer). Other criteria will be easily deduced for other postures.
- CRI is the criterion
- Abs the absolute value operator
- d the derived signal from a sensor
- t the time
- k a predefined constant
- Sign the sign operator the device 15 will have a zero output if the result of the calculation is less than a negative threshold, which corresponds to a fast reversal of the direction of movement, and an output equal to the unit otherwise.
- the validation module 18 When the signal of the device 15 is zero, the validation module 18, which is a multiplier, outputs a null signal and therefore inhibits the calculations of the physiological activity; otherwise, when the device 15 emits a signal equal to 1, the validation module 18 has no influence on the signal passing through it and passes it without modifying it.
- the estimation device 16 aims to isolate a component of the signal of each sensor 4 or 5 which is representative of the activity of the carrier. It may be a filter such as a low-pass filter, or, more interestingly, a non-stationary filter for not filtering the signal in the presence of a signal reversal point corresponding to a rapid inversion of its evolution.
- An F filter using a sigmoid function can be used. This process is based on the notion that the signal can be filtered without inconvenience when it is stable, but that it should not be filtered situations of great instability where the activity of the wearer also includes movements of higher frequency.
- a sigmoid function tends to 0 for input values close to 0 and tends to 1 for very large input values.
- An example is 1 / (1 + e -x ), but functions like arcsin, arctg, and so on. are others.
- a filter of the input signal noted s (t) can be a low pass filter weighted by the criterion CRI met above:
- F S t sigmoid SHOUT . s t + 1 - sigmoid SHOUT ⁇ F ⁇ S t past - low .
- the sigmoid is 1 / (1 + e -x )
- the subtracter 17 has a positive terminal which receives the normalized signal and a negative terminal which receives the signal supplied by the estimation device 16. The difference corresponds to the signal representative of the physiological activity.
- the validation module 18 is a multiplier that leaves this signal unchanged in circumstances considered normal and cancels it otherwise.
- the choice device 19 makes it possible to choose the signals which are the most representative of the movement of the breathing according to the posture of the wearer 2 estimated by the posture analysis device 14.
- the movements due to the breathing will be estimated by the sensitive accelerometers 4 in the direction Y and Z, and by the magnetometers 5 in the X and Z directions; otherwise, with the wearer 2 standing or sitting, the accelerometers 4 will be considered in the X and Z directions and the magnetometers 5 in the Y and Z directions. This will eliminate the accelerometers influenced by the acceleration of gravity and which would provide measures too noisy.
- the heart rate extractor 20 is a bandpass filter whose limits are, for example, 0.5 Hertz and 3 Hertz.
- the device 21 for calculating the core frequency advantageously uses the accelerometers 4 and in particular the one that is oriented in the X direction. The period is calculated by detecting the consecutive maximums and estimating the durations that separate them. These maximums are produced by the main pulse of the heart; they have a width of about 30 milliseconds and are separated on average by a duration of about 0.8 seconds for a person at rest.
- the detection can be improved by applying filtering adapted to the shape of the maximums to be detected, for example a filter of width equivalent to 250 milliseconds which is at a value equal to 1 in the center over an equivalent width of 30 milliseconds, and 0 at the periphery .
- the frequency of the heart is equal to the inverse of the duration separating the maximums.
- a sliding average calculation can be performed taking into consideration the average of a few previously measured frequencies.
- the output device 22 is generally a transmitter directing the results obtained to a visualization or diagnostic device outside the detector 1.
- the device for extracting the respiratory component 23 also consists of a band-pass filter between the frequencies, for example 0.03 hertz and 1 hertz.
- the respiratory rate calculating device 24 uses the results of one or more sensors 4 and 5 and calculates the respiratory rate by estimating the time between three consecutive zero crossings of a respiratory signal; the frequency is the inverse of this duration.
- a sliding average calculation may be performed to improve the results, or an average of calculation on several sensors 4 and 5.
- the output device 25 is still a transmitter of the results obtained to an external means of visualization or diagnosis, or a means of synchronization of another device on the respiratory cycle.
- magnetometers may be differential probes (fluxgates) or giant magneto-resistors.
- the detector comprises a plurality of sensors distributed for example in different parts of the body, each sensor being connected to the signal processing unit 6 for example, by electrical connection, by radio frequency.
- the advantage of this embodiment is to overcome the inability of a sensor to give physiological information, for example in the case where the patient is pressed on a sensor, which can not then measure breathing. Other sensors located elsewhere are used. The number of sensors used, their degree of redundancy and their locations are not critical.
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Abstract
Description
Le sujet de cette invention est un détecteur portatif destiné à mesurer des mouvements de la personne porteuse.The subject of this invention is a portable detector for measuring movements of the wearer.
Un art antérieur abondant existe pour mesurer des signaux cardiaques ou autres au moyen d'un détecteur qu'on colle sur le patient. Des capteurs de mouvement comme des accéléromètres ont ainsi été proposés pour suivre le mouvements de la cage thoracique et en déduire le rythme cardiaque. De tels détecteurs ont cependant été réservés à des conditions particulières d'état ou de posture du patient ; en général, une absence d'effort ou de mouvement est nécessaire pour donner une mesure fiable, qui ne soit pas brouillée par des composantes d'autre origine du signal de mouvement, qui pourraient être prépondérantes à cause de la petitesse des mouvements d'origine cardiaque.An abundant prior art exists for measuring cardiac or other signals by means of a detector which is adhered to the patient. Motion sensors such as accelerometers have been proposed to monitor the movement of the chest and deduce the heart rate. Such detectors have, however, been reserved for particular conditions of state or posture of the patient; in general, an absence of effort or movement is necessary to give a reliable measurement, which is not scrambled by components of other origin of the motion signal, which could be preponderant because of the smallness of the movements of origin heart.
On a aussi appliqué des capteurs de mouvement à divers endroits du corps pour suivre les personnes porteuses et parfois déterminer un état de sommeil, une chute, etc. La complexité des postures et des niveaux d'activité humaine ne se prête pas à une analyse réelle de l'activité avec les détecteurs usuels, qui sont plutôt réservés à la détection d'un seul genre d'événements et programmés pour ignorer les autres, dans la mesure du possible.Motion sensors have also been applied to various parts of the body to track the surrogate and sometimes to determine sleep, falling, etc. The complexity of postures and levels of human activity does not lend itself to a real analysis of the activity with the usual detectors, which are rather reserved for the detection of a single kind of events and programmed to ignore others, as far as possible.
Il serait intéressant, par exemple, de compléter un détecteur de chute par un détecteur de mesures physiologiques pour vérifier l'état du patient après la chute, mais cela n'est possible qu'avec des détecteurs respectifs tous deux portés par le patient ce qui est inconfortable.It would be interesting, for example, to complete a fall detector with a physiological measurement detector to check the patient's condition after the fall, but this is only possible with respective detectors both worn by the patient which is uncomfortable.
Un détecteur portatif perfectionné est proposé ici et comprend d'abord des moyens de traitement du signal permettant de distinguer une composante du signal, due à une activité extérieure du sujet porteur, d'au moins une composante du signal due à une activité physiologique (les battements du coeur ou le souffle notamment). Un tel dispositif est toutefois décrit par US-A-5 935 081.An improved portable detector is proposed here and comprises first signal processing means for distinguishing a component of the signal, due to an external activity of the carrier subject, of at least one component of the signal due to a physiological activity (the heart beat or breath especially). Such a device is however described by US-A-5 935 081.
Des objets de l'invention sont :
- de fournir un détecteur distinguant des composantes de signaux de niveaux bien différents et susceptible de varier fortement avec le temps ;
- de le faire à partir de mesures faites par des mêmes capteurs de mouvement ;
- de fournir un tel détecteur qui soit de structure unitaire et de petite taille ;
- d'offrir une capacité accrue de mesure et de diagnostic d'états physiologiques, en limitant les durées où les mesures ne doivent pas être considérées ;
- d'offrir une détermination plus universelle d'états de posture et d'activité du porteur en en discernant un plus grand nombre.
- to provide a detector distinguishing signal components of very different levels and likely to vary greatly over time;
- to do it from measurements made by the same motion sensors;
- to provide such a detector which is of unitary structure and of small size;
- to offer an increased ability to measure and diagnose physiological states, by limiting the times when measurements should not be considered;
- to provide a more universal determination of states of posture and activity of the wearer by discerning a greater number.
Il convient d'éviter qu'une détection incorrecte ne conduise à une alerte inutile. Une telle situation peut advenir avec certains mouvements extérieurs particulièrement brusques qui en pratique empêchent une détection convenable des mouvements d'origine physiologique. Il est donc utile et caractéristique de l'invention d'ajouter au détecteur un module reconnaissant une telle situation d'après des critères dépendant de la composante d'activité extérieure, et qui décide alors une invalidation temporaire de l'estimation de la composante due à l'activité physiologique.Incorrect detection should not result in an unnecessary alert. Such a situation may occur with certain particularly sudden external movements which in practice prevent proper detection of movements of physiological origin. It is therefore useful and characteristic of the invention to add to the detector a module recognizing such a situation according to criteria dependent on the external activity component, and which then decides a temporary invalidation of the component estimate due to physiological activity.
Les battements du coeur et le souffle sont des mouvements périodiques, dont l'intensité et la fréquence varient d'après le niveau d'activité du porteur dans des conditions particulières. Les mouvements dus à l'activité extérieure du porteur sont généralement à basse fréquence ; mais n'étant pas périodiques, ils sont compris dans une bande de fréquence plus large, et leur intensité peut varier fortement. En raison de ces variations de fréquence et plus encore des recouvrements de bandes de fréquence associées à ces différents mouvements, il est impossible de les séparer par de simples filtrages du signal. On a cependant obtenu des résultats satisfaisants en appliquant un filtre non-stationnaire au signal ou aux signaux de mouvement et en soustrayant le signal filtré du signal d'origine (le signal brut ou bien un signal ayant subi un filtrage préliminaire pour éliminer le bruit) : les signaux d'origine physiologique ressortent alors assez bien.The heartbeat and the breath are periodic movements, the intensity and frequency of which vary according to the level of activity of the wearer under particular conditions. Movements due to the outer activity of the wearer are generally low frequency; but not being periodic, they are included in a wider frequency band, and their intensity can vary greatly. Because of these frequency variations and moreover frequency band overlaps associated with these different movements, it is impossible to separate them by simple signal filtering. Satisfactory results, however, have been obtained by applying a non-stationary filter to the motion signal or signals and subtracting the filtered signal from the original signal (the raw signal or a pre-filtered signal to eliminate noise). : the signals of physiological origin come out quite well.
Un autre écueil provient de la sensibilité des mesures à la posture corporelle prise par le porteur, puisque l'accélération de la gravité, qui intervient dans les mesures accélérométriques et doit y être corrigée, est perçue avec une intensité qui dépend de cette posture, et que les mesures de l'activité physiologique donnent des valeurs d'accélération beaucoup plus faible. On préconise d'ajouter des indicateurs de la position du porteur, notamment des magnétomètres mesurant la direction du champ magnétique ambiant, afin de bien déterminer la posture de la personne porteuse et de choisir certains seulement des signaux de mouvement, tout en écartant ceux qui sont trop affectés par la gravité, pour le traitement conforme à l'invention. Ce perfectionnement est utile avant tout quand plusieurs capteurs mesurent autant de mouvements du porteur dans des directions différentes. Une situation courante consiste en l'emploi de trois capteurs mesurant des mouvements dans des directions perpendiculaires, usuellement d'avance, de côté et d'élévation du porteur.Another pitfall comes from the sensitivity of measurements to the body posture taken by the wearer, since the acceleration of gravity, which is involved in the accelerometric measurements and must be corrected, is perceived with an intensity that depends on this posture, and that measurements of physiological activity give much lower acceleration values. It is recommended to add indicators of the position of the wearer, including magnetometers measuring the direction of the ambient magnetic field, in order to determine the posture of the person carrying and select some only movement signals, while excluding those who are too much affected by gravity, for the treatment according to the invention. This improvement is useful above all when several sensors measure as many movements of the wearer in different directions. A common situation is the use of three sensors measuring movements in perpendicular directions, usually in advance, side and elevation of the wearer.
Une réalisation de l'invention sera maintenant décrite plus complètement en liaison aux figures. La figure 1 illustre la place du détecteur sur la personne porteuse, la figure 2 le détecteur dans son ensemble et la figure 3 le système de traitement.An embodiment of the invention will now be described more fully with reference to the figures. Figure 1 illustrates the position of the detector on the person carrying, Figure 2 the detector as a whole and Figure 3 the treatment system.
La figure 1 montre que le détecteur, portant la référence 1, est placé sur la poitrine d'un porteur 2. Il pourrait être placé sur l'abdomen ou ailleurs. Le détecteur 1 est miniature, ce qui lui permet d'être porté avec confort et sans presque être aperçu, contrairement à d'autres. Les axes X, Y et Z sont introduits pour la commodité de l'explication et définissent un repère lié au porteur 2, l'axe X étant dirigé vers l'avant, l'axe Z vers les pieds et l'axe Y vers la droite.Figure 1 shows that the detector, labeled 1, is placed on the chest of a
D'après la figure 2, le détecteur 1 peut comporter un boîtier 3 contenant trois accéléromètres portant tous la référence 4, trois magnétomètres portant tous la référence 5 et un système de traitement 6 auquel accéléromètres 4 et magnétomètres 5 sont reliés par des fils de manière à lui fournir leurs signaux. Les accéléromètres 4 mesurent chacun une composante d'accélération du mouvement de la poitrine du porteur 2 dans un des axes X, Y et Z respectivement en fonction de la direction de la gravité ; les magnétomètres 5 font de même en fonction de la direction du champ magnétique terrestre. Le détecteur 1 est maintenu à une orientation constante contre la peau ou un habit du porteur 2 par de la colle, une couture, une bande de serrage, ou tout autre moyen convenable. La description porte maintenant sur l'unité de traitement 6 à l'aide de la figure 3.According to FIG. 2, the
Les signaux issus des accéléromètres 4 ou des magnétomètres 5 passent chacun par un module de normalisation 7 et sont transmis à deux modules de calcul 8 et 9 travaillant à la fois en parallèle et en interaction dont le premier (8) calcule la composante des signaux qui est due à l'activité extérieure du porteur 2 et le second (9) calcule la composante des signaux due à l'activité physiologique ; ce second module 9 comprend un sous-module 10 affecté aux mouvements dus au battement du coeur et un sous-module 11 affecté aux mouvements dus au souffle respiratoire.The signals from the
Le premier module de calcul 8 comprend un filtre passe-bas 12 qui transmet le signal issu du module de normalisation 7 à un dispositif d'analyse d'activité 13, à un dispositif d'analyse de posture 14, à un dispositif d'analyse de niveau d'activité 15 et un dispositif d'estimation 16 de la composante d'activité. Le signal issu du module de normalisation 7 parvient aux sous-modules 10 et 11 après être passé par un soustracteur 17, un module de validation 18, et encore, pour le sous-module 11, par un dispositif de choix 19. Le sous-module 10 comprend un dispositif d'extraction de la composante cardiaque 20, un dispositif de calcul de fréquence 21 et un dispositif d'examen 22. Le sous-module 11 comprend un dispositif d'extraction de la composante de respiration 23, un dispositif de calcul de fréquence 24 et un dispositif de sortie 25.The
Ces différents éléments seront décrits successivement en détail. Le dispositif de normalisation 7 est d'un genre ordinaire qui permet de calibrer les signaux, par exemple selon une loi linéaire, pour fournir en sortie des signaux normalisés, qui sont proportionnels à l'accélération qu'ils subissent. Le filtre passe-bas 12 sert à éliminer les fréquences élevées du signal, qui n'expriment en pratique que des bruits. Le dispositif d'analyse d'activité 13 n'est pas indispensable et son contenu peut dépendre des genres d'activités qu'on cherche à diagnostiquer, comme la chute, le sommeil, la marche, le changement de position ou autres. Le diagnostic peut être effectué avec plusieurs capteurs 4 et 5. Le dispositif d'analyse de posture 14 permet de déterminer si le porteur 2 est debout, assis ou couché en comparant les accélérations mesurées par les accéléromètres 4. Si le signal le plus grand est mesuré par l'accéléromètre 4 en X ou l'accéléromètre 4 en Y, le porteur est couché mais il est assis ou debout si l'accélération en Z est prépondérante puisque la gravité est dirigée suivant cet axe. Le diagnostic de posture est établi si les rapports des accélérations sont supérieurs à certains coefficients. Si le porteur 2 est debout, la comparaison des mesures pour les magnétomètres 5 en X et en Y peut donner sa direction dans les points cardinaux. La chute peut être déterminée par une rotation rapide autour d'un axe vertical ou une accélération rapide en rotation par rapport au champ de pesanteur (mesuré avec un accéléromètre). D'autres critères seront facilement déduits pour d'autres postures.These different elements will be described successively in detail. The
Le dispositif d'analyse du niveau d'activité 15 est destiné à indiquer si l'activité du porteur 2 atteint un niveau au-delà duquel les résultats obtenus pour les mesures physiologiques sont jugés comme impossibles à obtenir correctement. Il peut consister en un filtre de dérivation appliqué aux signaux des capteurs 4 et 5 et fournit une sortie binaire. Si un signal dérivé est supérieur à un seuil, ce qui traduit une variation trop brutale de mouvement, le dispositif 15 fournit une sortie nulle, sinon la sortie est égale à l'unité. Une autre façon de procéder consistera à appliquer un critère glissant sur les signaux dérivés provenant des capteurs, selon la formule ci-dessous :
Quand le signal du dispositif 15 est nul, le module de validation 18, qui est un multiplicateur, sort un signal nul et inhibe donc les calculs de l'activité physiologique ; sinon, quand le dispositif 15 émet un signal égal à 1, le module de validation 18 n'a pas d'influence sur le signal le traversant et le laisse passer sans le modifier.When the signal of the
Le dispositif d'estimation 16 a pour but d'isoler une composante du signal de chaque capteur 4 ou 5 qui est représentative de l'activité du porteur. Il peut s'agir d'un filtre comme un filtre passe-bas, ou, de façon plus intéressante, d'un filtre non-stationnaire permettant de ne pas filtrer le signal en présence de point de rebroussement du signal correspondant à une inversion rapide de son évolution.The
Un filtre F utilisant une fonction sigmoïde peut être utilisé. Ce procédé repose sur la notion que le signal peut être filtré sans inconvénient quand il est stable, mais qu'il ne doit pas l'être dans des situations de grande instabilité où l'activité du porteur comporte aussi des mouvements de plus haute fréquence.An F filter using a sigmoid function can be used. This process is based on the notion that the signal can be filtered without inconvenience when it is stable, but that it should not be filtered situations of great instability where the activity of the wearer also includes movements of higher frequency.
Une fonction sigmoïde tend vers 0 pour des valeurs d'entrée proches de 0 et tend vers 1 pour des valeurs d'entrée très grandes. Un exemple est 1/(1+e-x), mais des fonctions comme arcsin, arctg, etc. en sont d'autres.A sigmoid function tends to 0 for input values close to 0 and tends to 1 for very large input values. An example is 1 / (1 + e -x ), but functions like arcsin, arctg, and so on. are others.
D'après ce qui précède, un filtre du signal d'entrée noté s(t) peut être un filtre passe-bas pondéré par le critère CRI rencontré plus haut :
D'autres fonctions de filtrage que F peuvent aussi être appliquées, de même que des filtres permettant d'extraire une composante à basse fréquence du signal qui maintienne les discontinuités. Un autre exemple de filtrage préconisé est celui qui est proposé dans l'article "Non linear anisotropic filtening of MRI data" IEEE Transactions on Médical Imaging, vol.11, n°2, p.231-232 par G. Gerig.Other filtering functions than F can also be applied, as well as filters for extracting a low-frequency component of the signal that maintains the discontinuities. Another example of recommended filtering is that proposed in the article "Non linear anisotropic filtening of MRI data" IEEE Transactions on Medical Imaging, Vol.11, No. 2, p.231-232 by G. Gerig.
Le soustracteur 17 a une borne positive qui reçoit le signal normalisé et une borne négative qui reçoit le signal fourni par le dispositif d'estimation 16. La différence correspond au signal représentatif de l'activité physiologique. Comme on l'a vu, le module de validation 18 est un multiplicateur qui laisse inchangé ce signal dans des circonstances jugées normales et l'annule autrement. Le dispositif de choix 19 permet de choisir les signaux qui sont les plus représentatifs du mouvement de la respiration en fonction de la posture du porteur 2 estimée par le dispositif d'analyse de posture 14. Si le porteur 2 est couché, les mouvements dus à la respiration seront estimés par les accéléromètres 4 sensibles dans la direction Y et Z, et par les magnétomètres 5 dans les directions X et Z ; sinon, le porteur 2 étant debout ou assis, on considérera les accéléromètres 4 dans les directions X et Z et les magnétomètres 5 dans directions Y et Z. On écartera par ce moyen les accéléromètres influencés par l'accélération de la gravité et qui fourniraient des mesures trop bruitées.The
L'extracteur de fréquence cardiaque 20 est un filtre passe-bande dont les limites sont, par exemple, 0,5 Hertz et 3 Hertz. Le dispositif 21 de calcul de la fréquence du coeur utilise avantageusement les accéléromètres 4 et notamment celui qui est orienté dans la direction X. La période est calculée en détectant les maximums consécutifs et en estimant les durées qui les séparent. Ces maximums sont produits par l'impulsion principale du coeur ; ils ont une largeur d'environ 30 millisecondes et sont séparés en moyenne par une durée d'environ 0,8 seconde pour une personne au repos. La détection pourra être améliorée en appliquant des filtrages adaptés à la forme des maximums à détecter, par exemple un filtre de largeur équivalente à 250 millisecondes qui est à une valeur égale à 1 au centre sur une largeur équivalente de 30 millisecondes, et 0 en périphérie. La fréquence du coeur est égale à l'inverse de la durée séparant les maximums. Un calcul de moyenne glissante pourra être effectué en prenant en considération la moyenne de quelques fréquences mesurées auparavant.The
Le dispositif de sortie 22 est généralement un émetteur dirigeant les résultats obtenus vers un dispositif de visualisation ou de diagnostic extérieur au détecteur 1.The
Le dispositif d'extraction de la composante respiratoire 23 consiste aussi en un filtre passe-bande entre les fréquences par exemple 0,03 hertz et 1 hertz. Le dispositif de calcul de fréquence respiratoire 24 utile les résultats d'un ou plusieurs capteurs 4 et 5 et calcule la fréquence respiratoire en estimant la durée entre trois passages par zéro consécutifs d'un signal respiratoire ; la fréquence est l'inverse de cette durée. Ici encore un calcul de moyenne glissante pourra être effectué pour améliorer les résultats, ou une moyenne de calcul sur plusieurs capteurs 4 et 5. Enfin, le dispositif de sortie 25 est encore un émetteur des résultats obtenus vers un moyen extérieur de visualisation ou diagnostic, ou encore un moyen de synchronisation d'un autre appareil sur le cycle respiratoire.The device for extracting the
Il n'est pas nécessaire de placer six capteurs de mouvement dans le détecteur 1 pour utiliser l'invention mais il est manifeste que la mesure des mouvements dans toutes les directions par deux séries de capteurs ayant des références différentes donne des résultats plus universels.It is not necessary to place six motion sensors in the
Ces magnétomètres pourront être des sondes différentielles (fluxgates) ou des magnéto-résistances géantes.These magnetometers may be differential probes (fluxgates) or giant magneto-resistors.
Dans un autre mode de réalisation, le détecteur comprend une pluralité de capteurs répartis par exemple en différents endroits du corps, chaque capteur étant relié à l'unité de traitement 6 de signaux par exemple, par connexion électrique, par radiofréquence. L'avantage de ce mode de réalisation est de pallier l'incapacité d'un capteur à donner une information physiologique, par exemple dans le cas om le patient est appuyé sur un capteur, qui ne peut plus alors mesurer la respiration. On utilise les autres capteurs situés ailleurs. Le nombre de capteurs utilisés, leur degré de redondance et leurs emplacements ne sont pas critiques.In another embodiment, the detector comprises a plurality of sensors distributed for example in different parts of the body, each sensor being connected to the
Claims (6)
- Portable detector (1) comprising at least one sensor (4, 5) collecting a movement signal from a person (2) wearing the detector, comprising signal processing means (6) for distinguishing a component of the signal due to an external activity of the wearer and at least one component of the signal due to a physiological activity of the wearer, characterized in that it comprises an invalidation decision module (15) for estimating the component due to the physiological activity based on a criterion that depends on the external activity component.
- Detector according to claim 1, characterized in that it comprises a filter receiving the movement signal, to estimate the component due to external activity, and a subtracting module (17), receiving the movement signal at a positive terminal and the signal output from the filter (16) at a negative terminal to estimate the component due to the physiological activity.
- Detector according to either of claims 1 or 2, characterized in that it comprises three sensors (4 or 5) collecting three perpendicular movement signals of the person, including one forward movement, one sideways movement and one upward movement.
- Detector according to any one of claims 1 to 3, characterized in that it comprises several sensors collecting corresponding movement signals including magnetometers, a wearer posture estimating module (14), and a sensor selection means to select some movement signals, that will be applied to processing means, and discard other movement signals, as a function of the wearer's posture.
- Detector according to claim 2, characterized in that the filter is non-stationary.
- Fall sensor characterized in that it comprises a detector according to any one of claims 1 to 5.
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Families Citing this family (61)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8403865B2 (en) | 2004-02-05 | 2013-03-26 | Earlysense Ltd. | Prediction and monitoring of clinical episodes |
US20070118054A1 (en) * | 2005-11-01 | 2007-05-24 | Earlysense Ltd. | Methods and systems for monitoring patients for clinical episodes |
US8942779B2 (en) | 2004-02-05 | 2015-01-27 | Early Sense Ltd. | Monitoring a condition of a subject |
US10194810B2 (en) | 2004-02-05 | 2019-02-05 | Earlysense Ltd. | Monitoring a condition of a subject |
US8491492B2 (en) | 2004-02-05 | 2013-07-23 | Earlysense Ltd. | Monitoring a condition of a subject |
CA2587875A1 (en) * | 2004-11-12 | 2006-05-18 | Andrew H. Elser V.M.D., Pc | Equine wireless physiological monitoring system |
US7616110B2 (en) * | 2005-03-11 | 2009-11-10 | Aframe Digital, Inc. | Mobile wireless customizable health and condition monitor |
WO2006123691A1 (en) * | 2005-05-18 | 2006-11-23 | Matsushita Electric Works, Ltd. | Sleep diagnostic system |
FR2886532B1 (en) * | 2005-06-07 | 2008-03-28 | Commissariat Energie Atomique | METHOD AND SYSTEM FOR DETECTING THE FALL OF A PERSON |
US7733224B2 (en) | 2006-06-30 | 2010-06-08 | Bao Tran | Mesh network personal emergency response appliance |
JP5120795B2 (en) * | 2005-11-15 | 2013-01-16 | 学校法人日本大学 | Human posture motion discrimination device and energy consumption calculation device |
US7602301B1 (en) | 2006-01-09 | 2009-10-13 | Applied Technology Holdings, Inc. | Apparatus, systems, and methods for gathering and processing biometric and biomechanical data |
US8652040B2 (en) | 2006-12-19 | 2014-02-18 | Valencell, Inc. | Telemetric apparatus for health and environmental monitoring |
US8157730B2 (en) * | 2006-12-19 | 2012-04-17 | Valencell, Inc. | Physiological and environmental monitoring systems and methods |
JP5539857B2 (en) * | 2007-04-19 | 2014-07-02 | コーニンクレッカ フィリップス エヌ ヴェ | Fall detection system |
US8585607B2 (en) | 2007-05-02 | 2013-11-19 | Earlysense Ltd. | Monitoring, predicting and treating clinical episodes |
FR2915890B1 (en) | 2007-05-07 | 2012-12-21 | Oreal | COMPOSITION FOR DYING KERATIN FIBERS COMPRISING AT LEAST ONE PARTICULATE AMINE SILICONE AND MONOETHANOLAMINE. |
US8251903B2 (en) | 2007-10-25 | 2012-08-28 | Valencell, Inc. | Noninvasive physiological analysis using excitation-sensor modules and related devices and methods |
US9883809B2 (en) | 2008-05-01 | 2018-02-06 | Earlysense Ltd. | Monitoring, predicting and treating clinical episodes |
US8882684B2 (en) | 2008-05-12 | 2014-11-11 | Earlysense Ltd. | Monitoring, predicting and treating clinical episodes |
EP2286395A4 (en) | 2008-05-12 | 2013-05-08 | Earlysense Ltd | Monitoring, predicting and treating clinical episodes |
US10052048B2 (en) * | 2008-05-14 | 2018-08-21 | Koninklijke Philips N.V. | Respiratory monitors and monitoring methods |
AU2009305075B2 (en) * | 2008-10-17 | 2014-09-11 | Koninklijke Philips Electronics N.V. | A fall detection system and a method of operating a fall detection system |
EP2189111A1 (en) * | 2008-11-21 | 2010-05-26 | Pulsion Medical Systems AG | Apparatus and method for determining a physiologic parameter |
JP5789199B2 (en) | 2009-02-25 | 2015-10-07 | ヴァレンセル,インコーポレイテッド | Headset and earbud |
US9750462B2 (en) | 2009-02-25 | 2017-09-05 | Valencell, Inc. | Monitoring apparatus and methods for measuring physiological and/or environmental conditions |
US8788002B2 (en) | 2009-02-25 | 2014-07-22 | Valencell, Inc. | Light-guiding devices and monitoring devices incorporating same |
DE102009019767B4 (en) | 2009-04-28 | 2017-07-20 | Universität Rostock | Device and method for fall detection |
AU2010269846B2 (en) | 2009-07-10 | 2014-10-02 | Koninklijke Philips Electronics N.V. | Fall prevention |
US8971936B2 (en) * | 2009-09-01 | 2015-03-03 | Adidas Ag | Multimodal method and system for transmitting information about a subject |
EP2533692B1 (en) * | 2010-02-11 | 2015-01-14 | Koninklijke Philips N.V. | Method and apparatus for determining a respiration signal |
US20120302900A1 (en) * | 2010-02-12 | 2012-11-29 | Koninklijke Philips Electronics N.V. | Method and apparatus for processing a cyclic physiological signal |
GB201009379D0 (en) | 2010-06-04 | 2010-07-21 | Univ Edinburgh | Method, apparatus, computer program and system for measuring oscillatory motion |
US20150342513A1 (en) * | 2010-07-01 | 2015-12-03 | Industrial Technology Research Institute | System and Method for Analyzing Biomechanics |
US9833171B2 (en) * | 2010-08-04 | 2017-12-05 | Koninklijke Philips N.V. | Monitoring of vital body signals during movement |
JP5742146B2 (en) * | 2010-09-13 | 2015-07-01 | 三菱化学株式会社 | INFORMATION PROCESSING METHOD, INFORMATION PROCESSING SYSTEM, INFORMATION PROCESSING DEVICE, DISPLAY DEVICE, INFORMATION PROCESSING PROGRAM, AND COMPUTER-READABLE RECORDING MEDIUM CONTAINING THE PROGRAM |
US10292625B2 (en) | 2010-12-07 | 2019-05-21 | Earlysense Ltd. | Monitoring a sleeping subject |
US8888701B2 (en) | 2011-01-27 | 2014-11-18 | Valencell, Inc. | Apparatus and methods for monitoring physiological data during environmental interference |
CN103429150B (en) * | 2011-03-11 | 2016-03-16 | 皇家飞利浦有限公司 | For monitoring the monitoring device of physiological signal |
US9427191B2 (en) | 2011-07-25 | 2016-08-30 | Valencell, Inc. | Apparatus and methods for estimating time-state physiological parameters |
EP2739207B1 (en) | 2011-08-02 | 2017-07-19 | Valencell, Inc. | Systems and methods for variable filter adjustment by heart rate metric feedback |
US8915868B1 (en) | 2011-08-11 | 2014-12-23 | Kendall Duane Anderson | Instrument for measuring the posture of a patent |
JP5895476B2 (en) * | 2011-11-29 | 2016-03-30 | 富士通株式会社 | Respiration measurement method and respiration measurement device |
JP5751162B2 (en) * | 2011-12-27 | 2015-07-22 | トヨタ自動車株式会社 | Respiration detection device |
BR112015008203A2 (en) | 2012-10-12 | 2017-07-04 | Inova Labs Inc | method and systems for the supply of oxygen enriched gas. |
EP2931125A4 (en) | 2013-01-28 | 2015-11-11 | Valencell Inc | Physiological monitoring devices having sensing elements decoupled from body motion |
DE102013011258A1 (en) * | 2013-07-05 | 2015-01-08 | Schneider Schreibgeräte GmbH | Device for determining the position of objects or persons |
US9153114B2 (en) * | 2014-02-07 | 2015-10-06 | Ge Yi | Fall detection method and system |
AU2015217160A1 (en) | 2014-02-14 | 2016-09-01 | 3M Innovative Properties Company | Activity recognition using accelerometer data |
US20150342518A1 (en) * | 2014-05-07 | 2015-12-03 | Andre Maxim Persidsky | System and method to monitor, guide, and evaluate breathing, utilizing posture and diaphragm sensor signals |
US20160029898A1 (en) | 2014-07-30 | 2016-02-04 | Valencell, Inc. | Physiological Monitoring Devices and Methods Using Optical Sensors |
WO2016022295A1 (en) | 2014-08-06 | 2016-02-11 | Valencell, Inc. | Optical physiological sensor modules with reduced signal noise |
EP3193715B1 (en) | 2014-09-15 | 2024-05-15 | Attenti Electronic Monitoring Ltd. | Impairment detection |
CA2961370A1 (en) | 2014-09-15 | 2016-03-24 | 3M Innovative Properties Company | Impairment detection with environmental considerations |
US9794653B2 (en) | 2014-09-27 | 2017-10-17 | Valencell, Inc. | Methods and apparatus for improving signal quality in wearable biometric monitoring devices |
US10945618B2 (en) | 2015-10-23 | 2021-03-16 | Valencell, Inc. | Physiological monitoring devices and methods for noise reduction in physiological signals based on subject activity type |
EP3344127A4 (en) | 2015-10-23 | 2018-07-25 | Valencell, Inc. | Physiological monitoring devices and methods that identify subject activity type |
WO2017095951A1 (en) | 2015-11-30 | 2017-06-08 | Nike Innovate C.V. | Apparel with ultrasonic position sensing and haptic feedback for activities |
WO2017192660A1 (en) | 2016-05-03 | 2017-11-09 | Inova Labs, Inc. | Method and systems for the delivery of oxygen enriched gas |
US10966662B2 (en) | 2016-07-08 | 2021-04-06 | Valencell, Inc. | Motion-dependent averaging for physiological metric estimating systems and methods |
GB2599816B (en) | 2017-06-16 | 2022-10-12 | Soter Analytics Pty Ltd | A system for monitoring core body movement |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4338950A (en) * | 1980-09-22 | 1982-07-13 | Texas Instruments Incorporated | System and method for sensing and measuring heart beat |
US5360436A (en) * | 1992-04-03 | 1994-11-01 | Intermedics, Inc. | Cardiac pacing responsive to multiple activity types |
US5354317A (en) * | 1992-04-03 | 1994-10-11 | Intermedics, Inc. | Apparatus and method for cardiac pacing responsive to patient position |
US5935081A (en) * | 1998-01-20 | 1999-08-10 | Cardiac Pacemakers, Inc. | Long term monitoring of acceleration signals for optimization of pacing therapy |
US6491647B1 (en) * | 1998-09-23 | 2002-12-10 | Active Signal Technologies, Inc. | Physiological sensing device |
US6703939B2 (en) * | 1999-09-15 | 2004-03-09 | Ilife Solutions, Inc. | System and method for detecting motion of a body |
US6734834B1 (en) * | 2000-02-11 | 2004-05-11 | Yoram Baram | Closed-loop augmented reality apparatus |
US6477421B1 (en) * | 2000-02-24 | 2002-11-05 | Pacesetter, Inc. | Method and apparatus for position and motion sensing |
US6522266B1 (en) * | 2000-05-17 | 2003-02-18 | Honeywell, Inc. | Navigation system, method and software for foot travel |
JP2001236583A (en) * | 2000-12-19 | 2001-08-31 | Matsushita Electric Ind Co Ltd | Safety confirmation system |
JP2002360522A (en) * | 2001-06-13 | 2002-12-17 | Japan Science & Technology Corp | Equipment for supporting safe life of single aged person |
GB0117169D0 (en) * | 2001-07-13 | 2001-09-05 | Isis Innovation | Respiration and heart rate monitor |
US20030163177A1 (en) * | 2002-01-18 | 2003-08-28 | Eggers Philip E. | System method and apparatus for localized heating of tissue |
US6942621B2 (en) * | 2002-07-11 | 2005-09-13 | Ge Medical Systems Information Technologies, Inc. | Method and apparatus for detecting weak physiological signals |
-
2003
- 2003-07-02 FR FR0350285A patent/FR2856913B1/en not_active Expired - Fee Related
-
2004
- 2004-06-29 JP JP2004192038A patent/JP2005066323A/en active Pending
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- 2004-06-30 DE DE602004006803T patent/DE602004006803T2/en not_active Expired - Lifetime
Non-Patent Citations (1)
Title |
---|
None * |
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